Power consumption reduction in medical devices employing multiple digital signal processors and different supply voltages

ABSTRACT

Power consumption in medical and battery powered devices is reduced through the use and operation of multiple digital signal processing systems and through the application of different supply voltages to analog and digital circuits, respectively. Each processor of the multiple systems performs at least one particular function in a predetermined time period. The multiple digital signal processors of such systems can be operated at lower clock frequencies relative to those that would be required by one of such processors to complete the multiple functions within the predetermined time period. With reduced clock frequency, power consumption is reduced. Further, with reduced clock speed, supply voltages applied to such digital signal processors may also be reduced. A source applies a first fixed supply voltage to the digital circuits of the medical or battery powered device and a voltage generation circuit (e.g., a charge pump circuit) having the first fixed supply voltage applied thereto is used for generating a second fixed supply voltage to be applied to analog circuits of the device. Power consumption may also be reduced through the operation of circuits at clock speeds of lower levels to adequately complete desired functions during predetermined time periods (e.g., blanking interval, upper rate interval, etc.) just-in-time prior to subsequent required functional processes; by providing supply voltages tailored for various circuits of an integrated circuit; by operating two or more circuits of an integrated circuit at different clock frequencies; by changing the supply voltage level “on the fly” as required by specific circuit timing functions required for various circuitry based on clock frequencies used to control operation of such circuitry; and/or by tailoring back gate bias or adjusting back gate bias “on the fly” for circuits based on the supply voltage level applied to the circuits.

CLAIM TO PRIORITY AND REFERENCE TO RELATED APPLICATION

This application is a Continuation-In-Part of, and claims priority andother benefits from the filing date of, U.S. patent appln. Ser. No.09/067,881 for “Power Consumption Reduction in Medical Devices UsingMultiple Supply Voltages and Clock Frequency Control” to Thompson, filedApril 29, 1998, now abandoned hereby incorporated by reference herein inits entirety.

FIELD OF THE INVENTION

The present invention relates to power consumption of integrated circuitdesigns such as circuits used in medical devices, particularlyimplantable devices. More particularly, the present invention pertainsto the use of multiple digital signal processors in such circuit designsto reduce power consumption.

BACKGROUND OF THE INVENTION

Various devices require operation with low power consumption. Forexample, hand-held communication devices require such low powerconsumption and, in particular, implantable medical devices require lowpower capabilities. With respect to implantable medical devices, forexample, microprocessor-based implantable cardiac devices, such asimplantable pacemakers and defibrillators, are required to operate witha lower power consumption to increase battery life and device longevity.

Generally, such low power devices are designed using complementary metaloxide semiconductor (CMOS) technology. CMOS technology is generally usedbecause such technology has the characteristic of substantially zero“static” power consumption.

Power consumption of CMOS circuits consists generally of two powerconsumption factors, namely “dynamic” power consumption and static powerconsumption. Static power consumption is only due to current leakage asthe quiescent current of such circuits is zero. Dynamic powerconsumption is the dominant factor of power consumption for CMOStechnology. Dynamic power consumption is basically due to the currentrequired to charge internal and load capacitances during switching,i.e., the charging and discharging of such capacitances. Dynamic power(P) equals: ½CV_(DD) ²F, where C is nodal capacitance, F is the clock orswitching frequency, and V_(DD) is the supply voltage for the CMOScircuit. As can be seen from the formula for calculating dynamic power(P), such dynamic power consumption of CMOS circuits is proportional tothe square of the supply voltage (V_(DD)). In addition, dynamic power(P) is proportional to switching or clock frequency (F).

In accordance with the formula for dynamic power consumption, it hasbeen effective conventionally in CMOS integrated circuit designs toscale down the supply voltage for an entire device (e.g., hybrid) orintegrated circuit (IC), i.e., operate the circuit at low supplyvoltages, to reduce power consumption for such designs. For example, inthe MEDTRONIC SPECTRAX® device of circa 1979, IC circuitry was poweredby one lithium iodine cell (as opposed to the two cells of the priorart). This reduced the supply voltage to 2.8 volts from 5.6 volts, thusreducing overhead current. Voltages required to be greater than 2.8volts were generated by a voltage doubler, or alternatively by a chargepump (e.g., output pacing pulses). Further, for example, in theMEDTRONIC SYMBIOS® device of circa 1983, logic circuitry was powered bya voltage regulator controlling the IC supply voltage to a “sum ofthresholds” supply. This regulator provided a supply to the IC (i.e.,V_(DD)) of several hundred millivolts above the sum of the n-channel andp-channel thresholds of the CMOS transistors making up the IC. Thisregulator was self calibrating regarding manufacturing variations of thetransistor thresholds.

Other devices have reduced power consumption in other varied manners.For example, various device designs have shut-down analog blocks and/orshut-off clocks to logic blocks not being used at particular times,thereby reducing power. Further, for example, microprocessor baseddevices have historically used a “burst clock” design to operate amicroprocessor at a very high clock rate (e.g., generally 500-1000Kilohertz (KHz)), for relatively short periods of time to gain thebenefit of a “duty cycle” to reduce average current drain. A much lowerfrequency clock (e.g., generally 32 KHz) is used for other circuitryand/or the processor when not in the high clock rate mode, i.e., burstclock mode. Many known processor based implanted devices utilize theburst clock technique. For example, implanted devices available fromMedtronic, Vitatron, Biotronic, ELA, Intermedics, Pacesetters,InControl, Cordis, CPI, etc., utilize burst clock techniques. A fewillustrative examples which describe the use of a burst clock areprovided in U.S. Pat. No. 4,561,442 to Vollmann et al., entitled“Implantable Cardiac Pacer With Discontinuous MicroprocessorProgrammable Anti Tachycardia Mechanisms and Patient Data Telemetry,”issued Dec. 31, 1985; U.S. Pat. No. 5,022,395 to Russie, entitled“Implantable Cardiac Device With Dual Clock Control of Microprocessor,”issued Jun. 11, 1991; U.S. Pat. No. 5,388,578 to Yomtov et al., entitled“Improved Electrode System For Use With An Implantable Cardiac PatientMonitor,” issued Feb. 14, 1995; and U.S. Pat. No. 5,154,170 to Bennettet al., entitled “Optimization for Rate Responsive Cardiac Pacemaker,”issued Oct. 13, 1992.

FIG. 1 represents a graphical illustration of energy/delay versus supplyvoltage for CMOS circuits such as a CMOS inverter 10 shown in FIG. 2 forillustrative purposes. The inverter 10 is provided with a supplyvoltage, V_(DD), which is connected to the source of a PMOS field effecttransistor (FET) 12. PMOS FET 12 has its drain connected to the drain ofan NMOS FET 14 whose source is connected to ground. In thisconfiguration, an input V_(i) applied to both the gates of FETs 12, 14is inverted to provide output V_(O). Simply stated, one clock cycle, orlogic level change, is used to invert the input V_(i) to V_(O).

As shown in FIG. 1, the circuit logic delay increases drastically as thesupply voltage is reduced to near one volt, as represented by delay line16 and energy/delay line 18. As such, reducing of the supply voltage(V_(DD)) continuously to lower levels is impractical because of the needfor higher supply voltages when higher frequency operation is required.For example, generally CMOS logic circuits must periodically providefunctionality at a higher frequency, e.g., burst clock frequency.However, as the supply voltage (V_(DD)) is decreased, such energyconsumption is reduced by the square of the supply voltage (V_(DD)) asis shown by energy consumption line 20. Therefore, speed requires ahigher supply voltage (V_(DD)) which is in direct conflict with lowpower consumption.

Other problems are also evident when lower supply voltages (V_(DD)) areused for CMOS circuit designs. When a lower supply voltage is selected,static leakage current losses may arise, particularly at lowerfrequencies, due to increased static leakage current losses. Varioustechniques for reducing power consumption in devices are known in theart, some examples of which may be found in at least some of thereferences listed in Table 1 below.

TABLE 1 Patent No. Inventor Issue Date 4,031,899 Renirie 28 June 19774,460,835 Masuoka 17 July 1984 4,561,442 Vollmann et al. 31 December1985 4,791,318 Lewis et al. 13 December 1988 5,022,395 Russie 11 June1991 5,154,170 Bennett et al. 13 October, 1992 5,185,535 Farb et al. 9February 1993 5,388,578 Yomtov et al. 14 February 1995 5,610,083 Chan etal. 11 March 1997

All references listed in Table 1 above are hereby incorporated byreference herein, each in its respective entirety. As those of ordinaryskill in the art will appreciate readily upon reading the Summary of theInvention, Detailed Description of the Embodiments, and claims set forthbelow, at least some of the devices and methods disclosed in thepublications, patents or patent applications referenced in the presentapplication, including those disclosed in the references listed in Table1 above, may be modified advantageously in accordance with the teachingsof the present invention.

SUMMARY OF THE INVENTION

The present invention has certain objects. That is, various embodimentsof the present invention provide solutions to one or more problemsexisting in the prior art respecting circuitry design having lower powerconsumption, particularly with respect to implantable medical devices.Those problems include: CMOS, CML, SOS, SOI, BICMOS, PMOS and/or NMOScircuits having excessive dynamic power consumption which reducesbattery life; the inability to utilize low voltage supply levelseffectively; lack of ability to provide adequate processing capabilitiessuch as high processing capabilities including telemetryuplink/downlink, morphology detection, initialization of devices, whilestill providing low processing capabilities such as sensing intrinsicbeats, pacing, low speed telemetry, with the desired power consumption;and the inability to provide circuit designs that operate at lowerfrequencies and thus lower power consumption as opposed to the use ofhigher speed clocks such as burst clocks.

In comparison to known techniques for reducing power consumption incircuit designs, various embodiments of the present invention mayprovide one or more of the following advantages: reduced powerconsumption through the use of multiple digital signal processing (DSP)systems; reduced power consumption through the use of a lower voltagesupply (V_(DD)); reduced power consumption by decreased clock frequencyfor circuit designs; increased longevity of circuits, particularlyimplantable device circuitry; provide a potential reduction in productsize; providing high performance processing designs with additionalfeatures or functions due to the ability to reduce power with respect toother “required” features and functions; reduced static powerconsumption; providing multi-processor designs and DSP designs havingadditional features or functions due to the ability to reduce power withrespect to other “required” features and functions; reduced currentdrain for an overall design, even when operating analog circuitry athigher supply voltages relative to the supply voltages applied todigital circuitry of the design.

Some embodiments of the invention include one or more of the followingfeatures: two or more digital signal processing systems; multipleprocessors, each performing functions at lower clock frequencies toreduce power consumption; a first and second digital signal processoroperating on data representative of analog inputs to perform respectivefirst and second functions at respective first and second clockfrequencies during a predetermined time period with the first and secondclock frequencies being such that the power consumed by the first andsecond digital signal processors during performance of such functions isless than the power that would be consumed if only one of the processorswere to perform the functions within the time period; multiple digitalsignal processors having supply voltages that are reduced based on thereduction of clock frequency for such processors; providing analoginputs, e.g., cardiac sense signals, to the multiple processors for usein performing functions such as T-wave, P-wave, and R-wave detection;one or more analog circuits of a medical device (e.g., an atrial senseamplifier, a ventricular sense amplifier, a T-wave amplifier, one ormore bandpass filters, one or more detection circuits, one or moresensor amplification circuits, one or more physiological signalamplification circuits, one or more output circuits, a battery monitorcircuit, and/or a power on reset circuit) and one or more digitalcircuits of the medical is device (e.g., a processor, a controllerand/or a memory) with the supply voltage applied to the analog circuitsbeing greater than that applied to the digital circuits; a source forapplying a first fixed supply voltage to digital circuits of a medicaldevice and a voltage generation circuit (e.g., a charge pump circuit)having the first fixed supply voltage applied thereto for generating asecond fixed supply voltage to be applied to analog circuits of themedical device; adjustment of back gate bias of digital circuits of themedical device; level shifting of signals being communicated betweenanalog circuits and digital circuits having different supply voltagesapplied thereto; employing various ones or combinations of the foregoingfeatures in CMOS, CML (Current Mode Logic), SOS (Silicon on Sapphire),SOI (Silicon on Insulator), BICMOS, PMOS and/or NMOS circuitry.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a graphical illustration showing energy/delay versus supplyvoltage for CMOS circuit operation.

FIG. 2 shows a prior art CMOS inverter which is used as a building blockin many CMOS circuit designs.

FIG. 3 is a block diagram of a just-in-time clocking system according tothe present invention.

FIGS. 4A-4C show timing illustrations for use in describing thejust-in-time clocking system of FIG. 3.

FIG. 5 is a block diagram illustration of a multiple supply voltagesystem according to the present invention.

FIG. 6 is a block diagram illustrating a variable supply voltage systemaccording to the present invention.

FIG. 7 is a block diagram of clock controlled processing circuitryaccording to the present invention.

FIG. 8 is a diagram illustrating an implantable medical device in abody.

FIG. 9 is a block diagram of the circuitry of a pacemaker for use inillustrating one or more embodiments of the present invention.

FIG. 10 is a schematic block diagram of an implantablepacemaker/cardioverter/defibrillator (PCD) for use in illustrating oneor more embodiments of the present invention.

FIG. 11 is a schematic block diagram illustrating a variablelock/variable supply voltage digital signal processing system accordingto the resent invention.

FIG. 12 is a schematic block diagram generally illustrating the systemof FIG. 11.

FIG. 13 is a schematic block diagram generally illustrating reduction inpower consumption using multiple digital signal processing systemsaccording to the present invention.

FIG. 14 is a schematic block diagram of a portion of cardiac pacemakerincluding sense amplifiers for receiving cardiac sense signals.

FIG. 15 is a two digital signal processing system embodiment of a systemaccording to FIG. 13 illustrating implementation of the sense amplifierfunctions illustrated in FIG. 14 according to the present invention.

FIG. 16 is a general schematic block diagram of a device according tothe present invention using different supply voltages for analog anddigital circuits of the device.

FIG. 17 is a more detailed schematic block diagram of one embodiment ofa pacemaker much like that shown in FIG. 9 according to the presentinvention wherein a lower supply voltage is applied to the digitalcircuits of the pacemaker with a charge pump being used to generate ahigher supply voltage to be applied to the analog circuits of thepacemaker.

FIG. 18 is a block diagram illustrating the use of digital signalprocessor(s) in the embodiment shown in FIG. 17.

DETAILED DESCRIPTION OF THE EMBODIMENTS

One embodiment of the present invention is first generally described inreference to FIGS. 3-15. More particularly, at least in part the use ofmultiple DSP systems to reduce power consumption is shown in thoseFigures.

FIG. 3 shows a general block diagram of a just-in-time clock system 30.Just-in-time clock system 30 includes integrated circuit 32 and clocksource 34. Integrated circuit 32 includes a plurality of circuits C1-Cn.Each circuit when operable is capable of performing one or more circuitfunctions. A function is defined herein as any operation performed onone or more inputs in a plurality of cycles that results in an output.Generally, the functions performed by the various circuits C1-Cn areusually, although not necessarily always, performed in a predeterminednumber of clock cycles. Clock source 34 is operable for providing clocksignals at a plurality of clock frequencies generally shown asclock1-clockn.

Circuits C1-Cn of integrated circuit 32 may include discrete functioncircuits (e.g., logic circuits for operating upon one or more inputs toimplement a particular function to provide one or more outputstherefrom), such as circuits operating on one input from a sensor toprovide a representative signal to further functional circuitry,transceiver circuitry, conversion circuitry, etc. Moreover, circuitsC1-Cn may comprise data processing circuitry capable of performingmultiple functions under program control. Alternatively, such circuitsC1-Cn may implement firmware (software) functions/routines that mustcomplete prior to some succeeding event or prior to the start of thenext function. For example, as described further herein with respect toillustrative embodiments of implantable medical devices, such circuitsmay include digital signal processing circuits, telemetryuplink/downlink circuitry, morphology detection circuitry, arrhythmiadetection circuitry, monitoring circuitry, pacing circuitry,microprocessors, and so on.

The functions performed by each of circuits C1-Cn are typically requiredto be completed in a particular time period prior to a next functionalprocess being undertaken. For example, one logic circuit may perform afunction in a predetermined time period to provide an output required byanother circuit, or for example, a function may need to be performed byprocessing circuitry during a particular period of time due to the needfor other processing to be performed by such processing circuitry. Inanother example pertaining especially to an implantable medical device,processing to complete a particular function may need to be performed ina portion of a particular time interval such as a blanking interval, anupper rate interval, an escape interval, or refractory interval of acardiac cycle, or further, such as during a pulse generator/ programmerhandshake.

Clock source 34 may be configured in any manner for providing clocksignals at a plurality of frequencies. Such a clock source may includeany number of clock circuits wherein each provides a single clock signalat a particular frequency, clock source 34 may include one or moreadjustable clock circuits for providing clock signals over a continuousrange of clock frequencies, and/or clock source 34 may include a clockcircuit that is operable to provide clock signals at discrete clockfrequencies as opposed to over a continuous range. For example, theclock source 34 may include oscillators, clock dividers, timers, clockcontrol circuitry or any other circuit elements required for providingclock signaling according to the present invention. Preferably, clocksource 34 is configured as a continuously oscillating low frequencyclock and a controllable on/off higher frequency clock.

Just-in-time controllable clock operation of the just-in-time clockingsystem 30 of FIG. 3 is described herein in reference to FIGS. 4A-4C. Asshown in FIG. 4A, time period (x) represents the time period in which acircuit, e.g., one of circuits C1-Cn, is required to complete one ormore functions. The same time period (x) is shown in FIG. 4B. The timeperiod x may be equated to any number of different time periods. Forexample, the time period may be the amount of time a processing circuithas to perform a particular detection function due to the need for adetection output by a certain point in time, may be a time periodrequired to complete a particular function by a certain logic circuit soas to provide a timely output to a digital signal processing circuit,may be a time period to complete a firmware (software) routine, etc.Moreover, time period x may correspond to a cardiac cycle or a partthereof.

As shown in FIG. 4B, and according to conventional processing, circuitfunctions were typically performed at a burst cycle frequency and, assuch, the function performed required a time period 60. Therefore, onlya small amount of time (e.g., time period 60) of the entire time periodx was used to perform the one or more functions requiring n cycles oftime to complete. In such a case, conventionally, such burst clocks wereat a substantially high clock rate, e.g., 500-1000 KHz, for such shortperiods of time to gain the benefit of a “duty cycle” to reduce averagecurrent drain. However, such high clock rates may not be required forcarrying out such functions, or all functions.

With just-in-time clocking according to the present invention, as shownin FIG. 4A, substantially the entire time period x is used to performthe one or more functions which are completed in n cycles. In otherwords, the clock frequency, e.g., one of clock1-clockn, for the circuitperforming the one or more functions during the time period x is setsuch that the one or more functions are completed in the maximum timeavailable for performing such functions, i.e., the clock frequency is atits lowest possible value. Stated another way, a lower frequency clockis employed such that the one or more functions are performedjust-in-time for other circuit or routine functionality to be performed.

In such a just-in-time manner, the clock frequency used to control theperformance of such functions by the particular CMOS, CML, SOS, SOI,BICMOS, PMOS and/or NMOS circuitry is lowered resulting in reduced powerconsumption by such circuitry. According to calculations of dynamicpower, the lower frequency results in proportional power reduction. Withthe lowering of the clock frequency, the integrated circuit 32 includingthe various circuits C1-Cn can be designed to operate at a lowerfrequency, e.g., as opposed to burst frequency, and also at variousother frequencies depending upon need.

It is preferred that use of substantially the entire predeterminedperiod of time result in completion of the one or more functions beingperformed prior to the end of the time period x as is represented byremainder time periods 55 in FIG. 4A. This remainder time period 55, forexample, is preferably near or about 0 seconds.

FIG. 4C shows an illustrative timing example for processing circuitrywhich performs multiple functions. For example, the cardiac cycle of apatient is represented in FIG. 4C as time period x. During time period71, i.e., during a QRS complex of the cardiac cycle, high speedprocessing is performed at a high clock frequency relative to a lowerclock frequency used to control operation of the processing circuitryduring time period y. During the time period y, when the processingcircuitry is operated at a lower clock frequency, such lower clockfrequency may be set such that the functions performed during z cyclesare performed in substantially the entire maximum time period availablefor such processing, i.e., time period y. Once again, a small remaindertime period 75 of the cardiac cycle time period x may exist. Such timeperiod may be, for example, in the range of about 1.0 millisecond toabout 10.0 milliseconds when the cardiac cycle is in the range of about400 milliseconds to about 1200 milliseconds.

FIG. 5 shows a general block diagram of a multiple supply voltage system100 wherein one or more supply voltages are available and tailored forapplication to various circuits in an IC. The multiple supply voltagesystem 100 includes integrated circuit 102 and supply voltage source106. Integrated circuit 102 includes circuits C1-Cn. Supply voltagesource 106 is operable for providing a plurality of supply voltagesV1-Vn. Each supply voltage from supply voltage source 106 is tailored tobe applied to one or more circuits of circuits C1-Cn. As illustrated,supply voltage V1 is applied to circuit C1, supply voltage V2 is appliedto circuit C2 and C3, and so forth.

The tailoring of the supply voltages V1-Vn to the particular circuitsC1-Cn is dependent upon the frequency at which the circuits C1-Cn arerequired to be operated. For example, and as previously described, thelogic delay of such CMOS, CML, SOS, SOI, BICMOS, PMOS and/or NMOScircuitry circuits C1-Cn increases drastically as the supply voltage isreduced to near 1 volt. If such logic delay is tolerable, the supplyvoltage provided to a particular circuit will drastically reduce thepower consumption for that particular circuit as the energy is reducedin proportion to the square of the supply voltage (V_(DD)). However, ifsuch logic delay is not tolerable, for example, if the logic circuitperforms a function that must be completed within a particular period oftime, the reduction of the supply voltage (V_(DD)) applied to such acircuit will be limited depending upon the acceptable logic delay.However, the supply voltage V_(DD) for any particular circuit can bereduced as low as possible yet meet adequate speed requirements.

Integrated circuit 102 may include various different circuits C1-Cn likethose described with reference to FIG. 3. The supply voltage source 106may be implemented using a variety of components and may include anynumber of voltage sources wherein each provides a single supply voltagelevel, may include one or more adjustable voltage sources for providingsupply voltage levels over a continuous range of levels, and/or mayinclude a voltage source that is operable to provide discrete supplyvoltage levels as opposed to levels over a continuous range. The supplyvoltage source may include a voltage divider, a voltage regulator, acharge pump, or any other elements for providing the supply voltagesV1-Vn. Preferably, the supply voltage source 106 is configured as acharge pump.

In the typical case, supply voltage (V_(DD)) is generally in the rangeof about 3 volts to about 6 volts. Preferably, and in accordance withthe present invention, the supply voltages V1-Vn are in the range ofabout 1 volt to about 3 volts dependent upon the particular CMOS, CML,SOS, SOI, BICMOS, PMOS and/or NMOS technology used. With reduction insupply voltage (V_(DD)), the threshold voltage (V_(T)) for the circuitsis also reduced. For example, with supply voltages in the range of about3 to about 6 volts, the threshold voltage for CMOS, CML, SOS, SOI,BICMOS, PMOS and/or NMOS devices is generally in the range of about 0.8volts to about 1.0 volt. Preferably, in implantable medical devices,lithium chemistries are utilized for implantable batteries. Such lithiumchemistries are generally in the range of about 2.8 volts to about 3.3volts and generally the CMOS, CML, SOS, SOI, BICMOS, PMOS and/or NMOScircuitry has an associated threshold voltage of about 0.75.

By reducing the supply voltages below about 2.8 volts, voltagethresholds for CMOS, CML, SOS, SO, BICMOS, PMOS and/or NMOS devices maybe decreased to as low as about 0.2 volts to about 0.3 volts. Currently,there are various ultra low power logic designs operating at a supplyvoltage as low as about 1.1 volts, as for example logic circuitry formicroprocessors for laptop and is other portable computer applications.By utilizing the tailored supply voltages V1-Vn, low power or ultra lowpower logic designs may be employed for at least some of the variouscircuits C1-Cn of integrated circuit 102. Other circuits may requirehigher supply voltages. With the use of lower threshold levels due tolower supply voltages, static power consumption losses undesirablyincrease by several orders of magnitude.

Multiple supply voltage system 100 may therefore further optionallyinclude back gate bias source 130 for providing back gate bias voltagesBV1-BVn to circuits C1-Cn of integrated circuit 102. Generally, backgate bias voltages BV1-BVn are dependent upon the supply voltage V1-Vnapplied to the circuits C1-Cn to adjust the threshold voltages fordevices of circuits C1-Cn. For example, the threshold voltage (V_(T))for the CMOS, CML, SOS, SOI, BICMOS, PMOS and/or NMOS devices of thecircuit may be at a lower value by providing a back gate bias voltage tothe particular circuits supplied with the lower supply voltage.Moreover, if circuit C1 is supplied with a lower supply voltage V1, thena back gate bias voltage BV1 may optionally be applied to circuit C1 toadjust the threshold voltage (V_(T)) for the CMOS, CML, SOS, SOI,BICMOS, PMOS and/or NMOS devices to a higher threshold voltage (V_(T))value. In such a manner, static leakage current losses can be minimizedbecause the equivalent higher threshold voltage has been restored.Moreover, a broader range of supply voltages is possible because theback gate adjustment allows a tailoring of the threshold allowinghigh/low speed operation and eliminating the static current drainleakage.

The back gate bias voltage may be provided by, for example, a fixedvoltage source (e.g., a charge pump) connected to the back gate well viaa contact. Alternatively, an active body bias scheme whereby the voltagesource is selectable or adjustable over an appropriate range may beused.

Back gate voltages may be applied in manners well know in the art. Theapplication of back gate bias voltages is described, for example, invarious patent references, including U.S. Pat. No. 4,791,318 to Lewis etal., U.S. Pat. No. 4,460,835 to Masuoka, U.S. Pat. No. 5,610,083 to Chanet al. and U.S. Pat. No. 5,185,535 to Farb et al., all incorporated byreference herein in their respective entireties.

FIG. 6 shows a general block diagram of a variable supplyvoltage/variable clock system 150 according to the present invention.System 150 includes integrated circuit 152, clock source 156, supplyvoltage source 154, and clock/supply voltage interface 155. Supplyvoltage source 154 is operable for providing a plurality of supplyvoltages V1-Vn to a plurality of circuits C1-Cn of integrated circuit152. Clock source 156 of system 150 is operable for providing clocksignals at a plurality of frequencies, clock1-clockn. Circuits C1-Cn areof a similar nature to those described with reference to FIG. 3. Clocksource 156 is similar to the clock source 34 as described with referenceto FIG. 3. Supply voltage source 154 is similar to supply voltage source106 described in reference to FIG. 5. In variable supplyvoltage/variable clock system 150, however, clock/voltage interface 155is employed to adjust supply voltages V1-Vn applied to the circuitsC1-Cn “on the fly,” as required by specific timing functions required byor inherent to circuits C1-Cn.

As an illustrative example, circuit C1 may be a particular logic circuitfor performing one or more particular functions. Such functions may berequired to be performed, however, in a first time period at a firstclock frequency and during a different second time period at a secondclock frequency so that such function may be performed within theallowed time of the respective first and second time periods. That is,one time period is shorter than the other and, as such, the functionswhich require performance over a certain number of cycles must beperformed at a higher clock frequency if it is to be completed within atime period that is shorter than another time period.

In such an example, and according to the present invention,clock/voltage interface 155 detects the clock signal applied to circuitC1 during the first time period in which the higher frequency clocksignal is used and accordingly provides supply voltage source 154 with asignal to select and apply a certain supply voltage corresponding to thehigher clock frequency. Thereafter, when the lower clock frequency isapplied to circuit C1 during the second time period, clock/voltageinterface 155 senses the use of the lower clock frequency and applies asignal to voltage supply source 154 for application of a certain supplyvoltage corresponding to the lower clock frequency for application tocircuit C1.

In another example, circuit C2 may be a CMOS, CML, SOS, SOI, BICMOS,PMOS and/or NMOS processor which may also have clock frequency andcorresponding supply voltage adjustments made “on the fly.” Such asystem will become readily apparent to those skilled in the art from thefollowing discussion referring to FIG. 7.

FIG. 7 shows a general block diagram of clock controlled processingsystem 200 according to the present invention. Clock controlledprocessing system 200 includes processor 202 (e.g., a CMOS, CML, SOS,SOI, BICMOS, PMOS and/or NMOS microprocessor or CMOS, CML, SOS, SOI,BICMOS, PMOS and/or NMOS digital signal processor), clock source 204,supply voltage source 206, voltage regulator 212, regulator interface210, clock control 208, and optional back gate bias source 214. In amanner similar to that described in reference to FIG. 6, the supplyvoltage 206 applied to processor 202 is changed “on the fly,” asrequired by specific circuit timing requirements.

Generally, processor 202 is operated under control of clock source 204.Depending upon the processing capability required, clock source 204 mayoperate processor 202 at any one of a plurality of clock frequencies.Such clock frequencies may be selected under the control of clockcontrol 208. Clock control 208 may be part of any timing and controlhardware and/or timing and control software used to control operation ofprocessor 202 as part of a larger system. Such clock control may takethe form, for example, of a digital controller/timer circuit forperforming timing control of an implantable medical device.

Processor 202 may perform any number of functions as appropriate for thedevice in which it is used. High frequency processing capabilities(i.e., about 250 KHz to about 10 MHz), low frequency processingcapabilities (i.e., about 1 Hz to about 32 KHz), and processingcapabilities with regard to frequencies between such limits arecontemplated according to the present invention. For simplicitypurposes, clock control processing system 200 operation shall bedescribed with reference to processor 202 performing only two differentfunctions, each during a predetermined respective period of time. Forexample, with respect to an implantable medical device such as apacemaker, during the first period of time, a high processing functionrequiring a relatively high clock frequency may include a function suchas telemetry uplink/downlink, morphology detection, initialization,arrhythmia detection, far-field R-wave detection, EMI detection,retrograde conduction, etc. On the other hand, low frequency processingfunctions may include a function such as sensing intrinsic beats,pacing, low speed telemetry, transtelephonic data transfer, remotemonitoring, battery checks, etc.

When processor 202 performs high frequency processing functions during apredetermined time period, a relatively high clock frequency (e.g.,about 250 KHz to about 10 MHz) may be supplied by clock source 204 foroperation of processor 202. Regulator interface 210 will detect thehigher clock frequency applied to processor 202 for operation during thehigh processing function and apply a control signal to voltage regulator212 for regulation of the supply voltage source 206. Supply voltagesource 206 is operable under control of voltage regulator 212 to providea supply voltage within a predetermined range, preferably between about1.1 volts and about 3 volts. When a high clock frequency is employed tooperate processor 202 for high frequency processing functions, supplyvoltage source 206 generally applies a supply voltage in the upper rangeof the preferred supply voltages to the CMOS, CML, SOS, SOI, BICMOS,PMOS and/or NMOS devices of processor 202.

On the other hand, when processor 202 executes low frequency processingfunctions during predetermined periods of time, clock control 208signals clock source 204 to apply a lower frequency for operation ofprocessor 25 202. As such, regulator interface 210 detects the lowerfrequency being used to operate processor 202 and issues a controlsignal to voltage regulator 212 for regulation of supply voltage source206 such that a lower supply voltage in the lower end of the preferredrange of supply voltages is applied to the CMOS, CML, SOS, SOI, BICMOS,PMOS and/or NMOS devices of processor 202.

It will be recognized by those skilled in the art that any intermediateprocessing capability may be achieved between the higher frequency andthe lower frequency capabilities described hereinabove, and that thescope of the present invention is not limited to processing at only twoclock frequencies and at two corresponding supply voltages. Instead,multiple levels of processing capability may be achieved according tothe present invention with associated clock frequencies andcorresponding supply voltages being applied to processor 202.

FIG. 4C illustrates one embodiment of the clock control processingsystem 200 of the present invention. As shown in FIG. 4C, during theoverall cardiac cycle of predetermined time period x, a high frequencyis employed to control operation of processor 202 during time period 71of the cardiac cycle time period x (e.g., during processing of the QRScomplex). Thereafter, a lower clock frequency is used during time periody for controlling operation of processor 202 to perform any of a numberof other different functions, such as cardiac event/EMI differentiationfunctions. During operation of the processor 202 at the higher clockfrequency during time period 71, a higher supply voltage from supplyvoltage source 206 is applied to the CMOS, CML, SOS, SOI, BICMOS, PMOSand/or NMOS circuitry devices of processor 202. Likewise, duringoperation of the processor 202 at the relatively lower clock frequency,a lower supply voltage from supply voltage source 206 is applied to theCMOS, CML, SOS, SOI, BICMOS, PMOS and/or NMOS devices of processor 202during time period y of the overall cardiac cycle time period x.

Moreover, and as shown in FIG. 7, an optional back gate bias 214 may beused to dynamically adjust the threshold voltage (V_(T)) of CMOS, CML,SOS, SOI, BICMOS, PMOS and/or NMOS circuitry devices of processor 202 asa function of the clock frequency applied to processor 202 by clocksource 204. The regulator interface 210 detects the clock frequency usedto control operation of processor 202 and controls the voltage level ofback gate bias 214 to be applied to the CMOS, CML, SOS, SOI, BICMOS,PMOS and/or NMOS devices of processor 202. The dynamic adjustment of thethreshold voltage may be implemented as an adjustable or selectablevoltage source utilizing, for example, a charge pump and a regulator.The back gate voltage and the “normal” gate voltage provide a gate biasor voltage to the transistor. By adjusting the back gate voltage, the“apparent” voltage is increased with a resultant reduction in leakagecurrent.

FIG. 8 is a simplified diagram of implantable medical device 260 forwhich the present invention finds particularly efficacious application.Implantable medical device 260 is implanted in body 250 near human heart264. Implantable medical device 260 is connected to heart 264 by leads262. In the case where device 260 is a pacemaker, leads 262 may bepacing and sensing leads for sensing electrical signals attendant to thedepolarization and repolarization of heart 264, and for providing pacingpulses in the vicinity of the distal ends thereof.

Implantable medical device 260 may be any implantable cardiac pacemakersuch as those disclosed in U.S. Pat. No. 5,158,078 to Benneft et al.,U.S. Pat. No. 5,387,228 to Shelton, U.S. Pat. No. 5,312,453 to Sheltonet al., or U.S. Pat. No. 5,144,949 to Olson, all hereby incorporatedherein by reference in their respective entireties and which can all bemodified according to the present invention.

Implantable medical device 260 may also be apacemaker/cardioverter/defibrillator (PCD) corresponding to any of thevarious commercially-available implantable PCDs, one of which issummarily described herein with reference to FIG. 10 and described indetail in U.S. Pat. No. 5,447,519. In addition to the PCD described inU.S. Pat. No. 5,447,519, the present invention may be practiced inconjunction with PCDs such as those disclosed in U.S. Pat. No. 5,545,186to Olson et al., U.S. Pat. No. 5,354,316 to Keimel, U.S. Pat. No.5,314,430 to Bardy, U.S. Pat. No. 5,131,388 to Pless, or U.S. Pat. No.4,821,723 to Baker et al., all hereby incorporated herein by referencein their respective entireties. Those devices may be employed using thepresent invention in that such devices may employ or be modified withcircuitry and/or systems according to the present invention.

Alternatively, implantable medical device 260 may be an implantablenerve stimulator or muscle stimulator such as those disclosed in U.S.Pat. No. 5,199,428 to Obel et al., U.S. Pat. No. 5,207,218 to Carpentieret al., or U.S. Pat. No. 5,330,507 to Schwartz, or an implantablemonitoring device such as that disclosed in U.S. Pat. No. 5,331,966issued to Bennet et al., all of which are hereby incorporated byreference herein in their respective entireties.

Finally, implantable medical device 260 may be a cardioverter, animplantable pulse generator (IPG) or an implantablecardioverter-defibrillator (ICD).

It is to be understood, however, that the scope of the present inventionis not limited to implantable medical devices or medical devices only,but includes any type of electrical device which employs CMOS, CML(Current Mode Logic), SOS (Silicon on Sapphire), SOI (Silicon onInsulator), BICMOS, PMOS and/or NMOS circuitry or circuit design wherelow power consumption is desired.

In general, implantable medical device 260 includes anhermetically-sealed enclosure that includes an electrochemical cell suchas a lithium battery, CMOS circuitry that controls device operations,and a telemetry transceiver antenna and circuit that receives downlinkedtelemetry commands from and transmits stored data in a telemetry uplinkto an external programmer. The circuitry may be implemented in discretelogic and/or may include a microcomputer-based system with A/Dconversion.

It is to be understood that the present invention is not limited inscope to particular electronic features and operations of particularimplantable medical devices and that the present invention may be usefulin conjunction with various implantable devices. Moreover, the presentinvention is not limited in scope to implantable medical devicesincluding only a single processor but may be applicable tomultiple-processor devices as well.

FIG. 9 shows a block diagram illustrating the components of pacemaker300 in accordance with one embodiment of the present invention.Pacemaker 300 has a microprocessor-based architecture. Illustrativepacemaker 300 of FIG. 9 is only one exemplary embodiment of suchdevices, however, and it will be understood that the present inventionmay be implemented in any logic-based, custom integrated circuitarchitecture or in any microprocessor-based system.

In the illustrative embodiment shown in FIG. 9, pacemaker 300 is mostpreferably programmable by means of an external programming unit (notshown in the figures). One such programmer suitable for the purposes ofthe present invention is the commercially available Medtronic Model 9790programmer. The programmer is a microprocessor-based device whichprovides a series of encoded signals pacemaker 300 by means of aprogramming head which transmits radio frequency (RF) encoded signals toantenna 334 pacemaker 300 according to a telemetry system such as, forexample, that described in U.S. Pat. No. 5,127,404 to Wybomy et al., thedisclosure of which is hereby incorporated by reference herein in itsentirety. It is to be understood, however, that any programmingmethodology may be employed so long as the desired information istransmitted to and from the pacemaker. Pacemaker device 300illustratively shown in FIG. 9 is electrically coupled to the patient'sheart 264 by leads 302. Lead 302 a including electrode 306 is coupled toa node 310 in the circuitry pacemaker 300 through input capacitor 308.Lead 302 b is coupled to pressure circuitry 354 of input/output circuit312 to provide a pressure signal from sensor 309 to the circuit 354. Thepressure signal is used to ascertain metabolic requirements and/orcardiac output of a patient. Further, activity sensor 351, such as apiezoceramic accelerometer, provides a sensor output to activity circuit352 of input/output circuit 312. The sensor output varies as a functionof a measured parameter that relates to metabolic requirements of apatient. Input/output circuit 312 contains circuits for interfacing toheart 264, to activity sensor 351, to antenna 334, to pressure sensor309 and circuits for application of stimulating pulses to heart 264 tocontrol its rate as a function thereof under control ofsoftware-implemented algorithms in microcomputer unit 314.

Microcomputer unit 314 preferably comprises on-board circuit 316 thatincludes microprocessor 320, system clock circuit 322, and on-boardrandom access memory (RAM) 324 and read only memory (ROM) 326. In thisillustrative embodiment, off-board circuit 328 comprises a RAM/ROM unit.On-board circuit 316 and off-board circuit 328 are each coupled by acommunication bus 330 to digital controller/timer circuit 332.

According to the present invention, the circuits shown in FIG. 9 arepowered by an appropriate implantable battery supply voltage source 301(e.g., a voltage source generally shown in FIGS. 1-7). For the sake ofclarity, the coupling of supply voltage source 301 to various circuitspacemaker 300 is not shown in the figures. Further, the circuitsoperable under control of a clock signal shown in FIG. 9 are operatedaccording to the present invention under clock source 338. For the sakeof clarity, the coupling of such clock signals from the clock source 338(e.g., a clock source generally shown in FIGS. 1-7) to such CMOS, CML,SOS, SOI, BICMOS, PMOS and/or NMOS circuits of pacemaker 300 is notshown in the Figures.

Antenna 334 is connected to input/output circuit 312 to permituplink/downlink telemetry through RF transmitter and receiver unit 336.Unit 336 may correspond to the telemetry and program logic disclosed inU.S. Pat. No. 4,556,063 issued to Thompson et al., hereby incorporatedby reference herein in its entirety, or to that disclosed in theabove-referenced Wyborny et al. patent.

V_(REF) and bias circuit 340 generates a stable voltage reference andbias currents for circuits of input/output circuit 312.Analog-to-digital converter (ADC) and multiplexer unit 342 digitizeanalog signals and voltages to provide “real-time” telemetryintracardiac signals and battery end-of-life (EOL) replacement function.A power on reset circuit 341 functions as a means to reset circuitry.

Operating commands for controlling the timing pacemaker 300 are coupledby bus 330 to digital controller/timer circuit 332, where digital timersand counters establish the overall escape interval of pacemaker 300 aswell as various refractory, blanking, and other timing windows forcontrolling the operation of the peripheral components disposed withininput/output circuit 312.

Digital controller/timer circuit 332 is preferably coupled to sensecircuitry 345 and to electrogram (EGM) amplifier 348 for receivingamplified and processed signals sensed by electrode 306 disposed on lead302 a. Such signals are representative of the electrical activity of thepatient's heart 264. Sense amplifier 346 of circuitry 345 amplifiessensed electrocardiac signals and provides an amplified signal to peaksense and threshold measurement circuitry 347. Circuit 347 in turnprovides an indication of peak sensed voltages and measured senseamplifier threshold voltages on path 357 to digital controller/timercircuit 332. An amplified sense amplifier signal is also provided tocomparator/threshold detector 349. The sense amplifier may correspond tothat disclosed in U.S. Pat. No. 4,379,459 to Stein, which is herebyincorporated by reference herein in its entirety.

The electrogram signal provided by EGM amplifier 348 is employed whenthe implanted device 300 is being interrogated by an external programmer(not shown) to transmit by uplink telemetry a representation of ananalog electrogram of the patient's electrical heart activity. Suchfunctionality is, for example, shown in U.S. Pat. No. 4,556,063 toThompson et al., previously incorporated by reference.

Output pulse generator and amplifier 350 provides pacing stimuli to thepatient's heart 264 through coupling capacitor 305 and electrode 306 inresponse to a pacing trigger signal provided by digital controller/timercircuit 332. Output amplifier 350 may correspond generally to the outputamplifier disclosed in U.S. Pat. No. 4,476,868 to Thompson, alsoincorporated by reference herein in its entirety. The circuits of FIG. 9comprise CMOS, CML, SOS, SOI, BICMOS, PMOS and/or NMOS circuitry capableof operation according to the present invention include processor 320,digital controller timer circuit 332, RAM 324, ROM 326, RAM/ROM unit 328and ADC/Mux 342.

FIG. 10 is a functional schematic diagram from U.S. Pat. No. 5,447,519to Peterson, which shows implantable PCD 400 in which the presentinvention may usefully be practiced. This diagram is an illustration tobe taken only as an exemplary type of device in which the invention maybe embodied, and not as limiting to the scope of the present invention.Other implantable medical devices as previously described havingfunctional organizations wherein the present invention may be useful mayalso be modified in accordance with the present invention. The presentinvention is also believed to be useful, for example, in conjunctionwith implantable PCDs such as those disclosed in U.S. Pat. No.4,548,209to Wielders et al.; U.S. Pat. No. 4,693,253 to Adams et al.; U.S. Pat.No. 4,830,006 to Haluska et al.; and U.S. Pat. No. 4,949,730 to Pless etal.; all of which are incorporated herein by reference in theirrespective entireties.

Illustrative PCD 400 is provided with six electrodes 401, 402, 404, 406,408, and 410. Electrodes 401 and 402 may be a pair of closely-spacedelectrodes, for example, that are positioned in the ventricle of heart264. Electrode 404 may correspond to a remote, indifferent electrodelocated on the housing of the implantable PCD 400. Electrodes 406, 408,and 410 may correspond to large surface area defibrillation electrodeslocated on leads to the heart 264 or epicardial electrodes.

Electrodes 401 and 402 are shown as hard-wired to the near field (i.e.,narrowly spaced electrodes) R-wave detector circuit 419 comprising bandpass filtered amplifier 414, auto threshold circuit 416 (for providingan adjustable sensing threshold as a function of the measured R-waveamplitude), and comparator 418. An Rout signal 464 is generated wheneverthe signal sensed between electrodes 401 and 402 exceeds a sensingthreshold defined by auto threshold circuit 416. Further, the gain onamplifier 414 is adjusted by pacer timer and control circuitry 420. Thesense signal, for example, is used to set the timing windows and toalign successive waveshape data for morphology detection purposes. Forexample, the sense event signal 464 may be routed through thepacer/timer control circuit 420 on bus 440 to processor 424 and may actas an interrupt for the processor 424 such that a particular routine ofoperations, e.g., morphology detection, discrimination functions, iscommenced by processor 424.

Switch matrix 412 is used to select available electrodes under controlof processor 424 via data/address bus 440 such that the selectionincludes two electrodes employed as a far field electrode pair (i.e.,widely spaced electrodes) in conjunction with a tachycardia/fibrillationdiscrimination function (e.g., a function to discriminate betweentachycardia, i.e., an abnormally fast heart rate, and fibrillation,i.e., uncoordinated and irregular heartbeats, so as to apply anappropriate therapy). Far field EGM signals from the selected electrodesare passed through band pass amplifier 434 and into multiplexer 432,where they are converted to digital data signals by analog to digitalconverter (ADC) 430 for storage in random access memory 426 undercontrol of direct memory access circuitry 428. For example, a series ofEGM complexes for several seconds may be performed.

According to the present invention, the circuits shown in FIG. 10 arepowered by an appropriate implantable battery supply voltage source 490(e.g., a voltage source generally shown in FIGS. 1-7). For the sake ofclarity, the coupling of supply voltage source 490 to various circuitsof the PCD 400 is not shown in the figures. Further, the circuitsoperable under control of a clock signal shown in FIG. 10 are operatedaccording to the present invention under clock source 491. For the sakeof clarity, the coupling of such clock signals from the clock source 491(e.g., a clock source generally shown in FIGS. 1-7) to such CMOS, CML,SOS, SOI, BICMOS, PMOS and/or NMOS circuits of PCD 400 is not shown inthe figures.

The occurrence of an R-wave sense event or detect signal Rout 464 iscommunicated to processor 424 to initiate morphology analysis onwaveforms by processor 424 for use in selection of a therapy for heart264. For example, the processor may calculate the cumulativebeat-to-beat variability of heart 264, time intervals separating R-wavesense events, and various other functions as set out in numerousreferences including any of the references already listed herein andvarious other references with regard to implantable PCDs.

Other portions of the PCD 400 of FIG. 10 are dedicated to the provisionof cardiac pacing, cardioversion, and defibrillation therapies. Withregard to cardiac pacing, the pacer timing/control circuit 420 includesprogrammable digital counters which control the basic timing intervalsassociated with cardiac pacing, including the pacing escape intervals,the refractory periods during which sensed R-waves are ineffective torestart timing of escape intervals, etc. The durations of such intervalsare typically determined by processor 424 and communicated to pacertimer/control circuit 420 via address/data bus 440. Further, undercontrol of processor 424, pacer timing/control circuit also determinesthe amplitude of such cardiac pacing pulses and pace out circuit 421provides such pulses to the heart.

In the event that a tachyarrhythmia (i.e., tachycardia) is detected, andan anti-tachyarrhythmia pacing therapy is desired, appropriate timingintervals for controlling generation of anti-tachycardia pacingtherapies are loaded from processor 424 into pacer timing and controlcircuitry 420. Similarly, in the event that generation of acardioversion or defibrillation pulse is required, processor 424 employsthe counters and timing and control circuitry 420 to control timing ofsuch cardioversion and defibrillation pulses.

In response to detection of fibrillation or a tachycardia requiring acardioversion pulse, processor 424 activatescardioversion/defibrillation control circuitry 454, which initiatescharging of the high voltage capacitors 456, 458, 460 and 462 viacharging circuit 450 under control of high voltage charging line 452.Thereafter, delivery of the timing of the defibrillation orcardioversion pulse is controlled by pacer timing/control circuitry 420.Various embodiments of an appropriate system for delivering andsynchronization of cardioversion and defibrillation pulses, andcontrolling the timing functions related to them is disclosed in moredetail in U.S. Pat. No. 5,188,105 to Keimel, which is incorporatedherein by reference in its entirety. Other such circuitry forcontrolling the timing and generation of cardioversion anddefibrillation pulses is disclosed in U.S. Pat. No. 4,384,585 to Zipes,U.S. Pat. No. 4,949,719 to Pless et al., and in U.S. Pat. No.4,375,817to Engle et al., all incorporated herein by reference in theirentireties. Further, known circuitry for controlling the timing andgeneration of anti-tachycardia pacing pulses is described in U.S. Pat.No. 4,577,633 to Berkovits et al., U.S. Pat. No. 4,880,005 to Pless etal., U.S. Pat. No. 4,726,380 to Vollmann et al., and U.S. Pat. No.4,587,970 to Holley et al., all of which are incorporated herein byreference in their entireties.

Selection of a particular electrode configuration for delivery of thecardioversion or defibrillation pulses is controlled via output circuit448 under control of cardioversion/defibrillation control circuit 454via control bus 446. Output circuit 448 determines which of the highvoltage electrodes 406,408 and 410 will be employed in delivering thedefibrillation or cardioversion pulse regimen.

The components of PCD 400 of FIG. 10 comprise CMOS, CML, SOS, SOI,BICMOS, PMOS and/or NMOS circuitry capable of operation according to thepresent invention include processor 424, control circuits 420 and 454,RAM 426, DMA 428, ADC 430, and multiplexer 432.

According to the present invention, pacemaker 300 illustrated in FIG. 9and PCD 400 illustrated in FIG. 10 may both be implemented in accordancewith the generalized embodiments previously described herein withreference to FIGS. 1-7. First, for example, with respect to pacemaker300 of FIG. 9, voltage supply source 301 of pacemaker 300 may beimplemented in a manner previously described with reference to FIGS.1-7. Likewise, clock source 338 of pacemaker 300 may be implemented insuch a manner as described with reference to FIGS. 1-7. Clock source 491of PCD 400 of FIG. 10 and the voltage supply source 490 of PCD 400 ofFIG. 10 may be implemented in accordance with the generalizedembodiments previously described herein with reference to FIGS. 1-7.

As one illustrative example, ADC/Mux 342, RF transmitter/receiver 336,digital controller timer circuit 332, and various other CMOS, CML, SOS,SOI, BICMOS, PMOS and/or NMOS circuits may be individually operated atdifferent clock frequencies available from clock source 338. Likewise,such circuits may be operated at corresponding supply voltages which maybe different for each of the circuits. Moreover, RF transmitter/receiver336 may be operated during a particular time period (e.g., whenuplinking) at a particular clock frequency available from clock source338 and at a particular supply voltage available from voltage supplysource 301 corresponding to the particular clock frequency. On the otherhand, during a different time period (e.g., during downlink), circuit336 may be operated at a completely different clock frequency and supplyvoltage. Automatic adjustment of telemetry parameters under certaincircumstances is described in U.S. Pat. No. 5,683,432 to Goedeke et al.,hereby incorporated by reference herein in its entirety.

In respect of FIG. 10, A/D converter circuit 430,cardioverter/defibrillator control circuit 454, and various othercircuits such as RAM 426, DMA 428, and multiplexer 432 may also beoperated at different clock frequencies available from clock source 491and at different corresponding supply voltages available from supplyvoltage source 490. A telemetry circuit (not shown in the Figures) maybe employed with PCD 400 of FIG. 10 and may also be operated atdifferent clock frequencies available from clock source 491 and atdifferent corresponding supply voltages available from supply voltagesource 490. Additionally, processor 424 may be operated at differentclock speeds, depending upon the function being performed by processor424 (such as described with reference to FIG. 7). Morphology detectionsensing at typical physiologic rates (i.e., 50 to 150 BPM), for example,may be performed at a first clock frequency and corresponding supplyvoltage while arrhythmia detection may be performed at a different clockfrequency and corresponding supply voltage. FIG. 11 shows variableclock/variable supply voltage digital signal processing (DSP) system 500which may be employed in conjunction with and/or in the alternative tocertain circuits shown in FIGS. 9 and 10. DSP system 500 according toFIG. 11, for example, may be employed in place of activity circuit 352,pressure circuit 354, sense amplifier circuit 346 (for P-wave, R-wave-and/or T-wave sense amplifiers), and further may be provided withadditional functionality with use of pseudo EKG signal 502. Generally,any number of analog signals 499, for example, such as pseudo EKGsignals 502, activity sensor signal 503 and pressure and onset sensorsignal 504, are provided through respective amplifiers 505-507. Theamplified signals are presented to multiplexer 510 which provides themto analog to digital converter (ADC) 516 of the digital signalprocessing system 500 in a cycled fashion.

Signals 502-504 may be cycled at different rates by cycling through theoutputs of the several amplifiers/preamplifiers 505-507 such asdescribed in pending U.S. patent application Ser. No. 08/801,335,Medtronic Docket No. P-4521, entitled “Method for Compressing DigitizedCardiac Signals Combining Lossless Compression and Non-linear Sampling,”which describes variable compression via ADC sampling and which isincorporated herein by reference in its entirety. The ADC may also havevariable conversion rates as described in U.S. Pat. No. 5,263,486 andU.S. Pat. No. 5,312,446, incorporated by reference herein in theirrespective entireties.

Input/output interface 514 and program registers 512 are utilized undercontrol of a timing circuit (not shown) to control application of theanalog signals from multiplexer 510 to ADC 516 of the DSP system 500which provides such converted digital signals to digital filter 518 toprovide a waveform for analysis to waveform analysis processor 520(i.e., a digital signal processor (DSP)) of system 500. To reduce power,the waveform analysis (DSP) processor 520 is clocked at differentspeeds, i.e., controlled “on the fly,” according to the presentinvention, depending upon the processing needs.

Only during a QRS complex, for example, does waveform analysis processor520 operate in a high speed processing mode at a relatively highfrequency. During the remainder of the cardiac cycle the DSP processor520 may be “idling along” at a much lower clock frequency. Such aprocessing cycle has been previously described with reference to FIG.4C. In addition to the lower clock speed utilized for different portionsof the cardiac cycle, one skilled in the art will recognize that inaccordance with the other aspects of the present invention, as the speedis reduced, the supply voltage level (V_(DD)) may also be reducedaccordingly. Thus, the objective of reduced power consumption isrealized.

DSP system 500 of FIG. 11 is generally shown in FIG. 12. Generally, DSPsystems, such as DSP system 500, may include an input filter, an ADC, asample and hold circuit (sometimes built into the ADC), and a digitalsignal processor to provide an output. The input filter, ADC, and sampleand hold circuit provide data representative of an analog input to theprocessor. The digital signal processor can then be used to implementone of various algorithms, such as, for example, digital filtering,mapping the input, performing morphology detection, functioning as senseamplifiers (P-wave, R-wave, or T-wave), etc., to provide a desiredoutput.

As used in a medical device described herein, the output of DSP system500 is generally provided to a controller in digital form. Such adigital output resulting from digital processing may, however, beconverted back into an analog output using components common to DSPsystems such as a digital to analog (DAC) converter, output filters,etc. One skilled in the art will recognize that depending upon theapplication of the present invention, the components of DSP system 500may vary. For example, one DSP system may include a DAC to provide ananalog output, while another such system may not.

As shown in FIG. 12, two or more analog input signals 499 aremultiplexed by multiplexer 510 and converted to digital datarepresentative thereof for processing by the digital signal processor ofDSP system 500. The data representative of the input signals is thenoperated upon by the digital signal processor of DSP system 500 toperform functions with regard thereto during a predetermined period oftime. R-wave detection algorithms and P-wave detection algorithms may beperformed, for example, by the same digital signal processor during thepredetermined time period using data representative of ventricular andatrial analog input signals, respectively, provided to the multiplexer510.

Such multiplexing of the input signals and use of a single digitalsignal processor as shown in FIGS. 11 and 12 to perform multiplefunctions in a predetermined period of time requires the digital signalprocessor of the DSP system 500 to be operated at a relatively highclock frequency. The clock frequency is relatively high compared to theclock frequencies that would be required if multiple digital signalprocessors were used to perform the functions in the same time period.With operation at a relatively high frequency to accomplish the multiplefunctions during this predetermined period of time, a relatively highsupply voltage must also be applied to the processor for operation.

The supply voltage is relatively high compared to the supply voltagethat would be required if multiple digital signal processors were usedto perform the functions in the same time period. As such, the dynamicpower (P) consumed by the single digital signal processor ((P)=½CV_(DD)²F, where C is nodal capacitance, F is the clock or switching frequency,and V_(DD) is the supply voltage for the processor) is rather high. Theformula for calculating dynamic power (P) indicates that dynamic powerconsumption of CMOS, CML, SOS, SOI, BICMOS, PMOS and/or NMOS circuits isproportional to the square of the supply voltage (V_(DD)). In addition,the dynamic power (P) is proportional to the switching or clockfrequency (F). As described below, the same multiple functions asperformed above using a single DSP system can be accomplished usingmultiple DSP systems operating at lower clock frequencies and lowersupply voltages to reduce power consumption.

FIG. 13 shows a generalized schematic illustration of such a multipleprocessor system 600 including multiple DSP systems 602-604 for reducingpower consumption according to the present invention. DSP system 602 isprovided with a first analog input signal 612 and includes conversioncircuitry for converting the analog input signal 612 to digital datarepresentative thereof. Digital signal processor 622 of the DSP system602 then operates on the data to perform a function and provide anoutput 632 (which may be converted back to an analog signal if desired).The digital signal processor 622 is operated at a first clock frequencyClk1 and a first supply voltage SV1 is applied to the digital signalprocessor 622.

DSP system 603 is provided with a second analog input signal 613 andincludes conversion circuitry for converting the analog input signal 613to digital data representative thereof. Digital signal processor 623 ofthe DSP system 603 then operates on the data to perform a function andprovide an output 633 (which may be converted back to an analog signalif desired). The digital signal processor 623 is operated at a secondclock frequency Clk2 and a second supply voltage SV2 is applied to thedigital signal processor 623.

Generally, the first and second clock frequencies Clk1 and Clk2 at whichthe first and second digital signal processors operate to perform theirrespective functions in a predetermined time period, are lower relativeto the clock frequency necessary for a single processor to perform thesame functions in the same predetermined time period. The first andsecond clock frequencies Clk1 and Clk2 are such that the power consumedby the first and second digital signal processors in performance of therespective functions during the predetermined period of time is lessthan the power that would be consumed if only one of the first andsecond digital signal processors were to perform both the respectivefunctions within the predetermined time period.

Likewise, supply voltage SV1 and SV2 may also be reduced because thedigital signal processors 622 and 623 are running at a lower speed and adecrease in clock frequency allows use of lower supply voltages aspreviously described herein. If the clock frequency Clk1 is reduced, forexample, SV1 applied to the digital signal processor 622 may also bereduced.

By way of example, consider the case in which system 600 includes onlyDSP system 602 and DSP system 603. Each of DSP systems 602 and 603receives a single analog input 612 and 613, respectively. Digital signalprocessor 622 operates on the data representative of analog input 612 atclock frequency Clk1 to perform a first function. Digital signalprocessor 623 operates on the data representative of the analog input613 at clock frequency Clk2 to perform a second function. In comparisonto the power consumed by a system such as that shown in FIG. 12 (where asingle processor is used to perform both the functions within thepredetermined period of time using multiplexed inputs), multiple digitalsignal processors may perform the same functions, but while consumingsubstantially less power.

More particularly, by using two digital signal processors in accordancewith the present invention, the dynamic power so consumed (P2) may becomputed by the formula:

(P2)=½(2C)(V _(DD)/2)²(F/2)

where C is two times the nodal capacitance because there are two digitalsignal processors, F/2 is the reduced clock or switching frequencybecause both the digital signal processors can operate at ½ the speed ascompared to a single processor attempting to complete both functions inthe predetermined period of time, and V_(DD)/2 is the supply voltagebecause the digital signal processors are running at ½ speed as comparedto the single processor attempting to complete both functions in thepredetermined time period.

Power consumed by the two digital signal processors illustration isgiven by the formula:

P2=½C(V _(DD) ²/4)F

which is ¼ the power consumed by the single processor using multiplexedinputs as described above in respect of FIG. 12. One skilled in the artwill now recognize that the foregoing two digital signal processorembodiment of the present invention occupies more integrated circuit diearea than a single processor having multiplexed inputs. Powerconsumption is greatly reduced, however.

In the illustrative embodiment described above, the clock frequencies atwhich the first and second digital signal processors operate aresubstantially equal. Those clock frequencies need not be the same orsubstantially the same, however, to reduce power consumption, and indeedmay be different. The first and second clock frequencies Clk1 and Clk2at which the first and second digital signal processors operate toperform the respective functions are most preferably frequenciesselected such that the power consumed by the first and second digitalsignal processors in performance of the respective functions during thepredetermined period of time is less than the power that would beconsumed if only one of the first and second digital signal processorswere to perform both of the functions within the predetermined timeperiod.

Moreover, and as shown in FIG. 13, more than two DSP systems, such asadditional DSP system 604, may be employed to reduce power consumption.Additionally, each of the digital signal processors, including DSPsystems 602-604, may be provided with one or more analog inputs asrepresented generally by inputs 618 which may be multiplexed asdescribed with respect to FIG. 11, or alternatively may be provided witha single input as shown above with respect to DSP systems 602 and 603.

Use of multiple DSP systems is particularly beneficial when processinghigher frequency analog signals, although such systems may be employedwith any analog signal. Such multiple DSP configurations findparticularly advantageous application, for example, when employed forP-wave, R-wave, and T-wave sensing, EMI detection, sensor signalprocessing of such signals as pressure, oxygen saturation, blood flowand cardiac contractility signals, telemetry functions, and the like.Such functions may be characterized generally by the bandwidth of theanalog signals being processed to perform such functions. In general,the bandwidth of analog signals such as cardiac sense signals is in therange of between about 10 Hz and about 100 Hz (as opposed to some sensorsignals, such as pressure signals, having a bandwidth of between about 1Hz and about 10 Hz).

FIGS. 14 and 15 illustrate the use of multiple DSP systems to performmultiple functions required for operation of a cardiac pacemaker. FIG.14 shows some components conventionally used in a cardiac pacemaker suchas that described in U.S. Pat. No. 5,387,228 to Shelton, entitled“Cardiac Pacemaker With Programmable Output Pulse Amplitude and Method,”issued Feb. 7, 1995. For simplicity, other components of the pacemaker,such as those previously described herein and which are also describedin other documents referenced herein such as in U.S. Pat. No. 5,387,228,are not described in further detail.

Referring again to FIG. 14, digital controller/timer circuit 731 iscoupled to sensing circuitry including sense amplifier circuit 738 and asensitivity control circuit 739. More particularly, digitalcontroller/timer circuit 731 receives an A-event (atrial event) signalon line 740, and a V-event (ventricular event) signal on line 741. Senseamplifier circuit 738 is coupled to leads 714 and 715 and receivesV-Sense (ventricular sense) and A-Sense (atrial sense) signals fromheart 764. Sense amplifier circuit 738 asserts the A-event signal online 40 when an atrial event (i.e., a paced or intrinsic atrial event)is detected, and asserts the V-event signal on line 741 when aventricular event (paced or intrinsic) is detected. Sense amplifiercircuit 738 includes one or more sense amplifiers corresponding, forexample, to that disclosed in U.S. Pat. No. 4,379,459 to Stein.Sensitivity control circuit 739 is provided to adjust the gain of senseamplifier circuit 738 in accordance with programmed sensitivitysettings, as will be appreciated by those skilled in art of pacing.

Ventricular electrocardiogram amplifier 742 is coupled to a conductor inlead 714 to receive a V-sense signal from heart 764. Similarly, atrialelectrocardiogram amplifier 743 is coupled to one conductor of lead 715to receive the A-sense signal from heart 764. The electrocardiogramsignals developed by amplifiers 742 and 743 are used on those occasionswhen the implanted device is being interrogated by an externalprogrammer for uplink telemetry.

FIG. 15 shows an embodiment of multiple DSP system 800 in accordancewith the present invention for replacing sensing circuitry 738 shown inFIG. 14. Multiple DSP system 800 includes two DSP systems 801 and 803.DSP system 801 includes a digital signal processor 841 which operates ondata representative of the A-sense signal 805 originating from theatrium of the heart. Further, DSP system 803 includes a digital signalprocessor 842 which operates on data representative of the V-sensesignal 807 originating from the ventricle of the heart. By way ofexample of the present invention, digital signal processor 841 detectswhen an atrial event (P-wave detection) occurs using the datarepresentative of the A-sense signal during a predetermined period oftime. In another example of the present invention, digital signalprocessor 843 detects when an ventricular event (R-wave detection)occurs using the data representative of the V-sense signal during thepredetermined period of time.

As shown in FIG. 15, the digital signal processors operate at clockfrequencies that are ½ of the clock frequency necessary for operation ofa single digital signal processor (assuming the corresponding singledigital signal processor receives, via a multiplexer, both A-sense andV-sense signals and performs both the atrial and ventricular detectionfunctions during the predetermined period of time). As such, and asdescribed above in the general two digital signal processorillustration, the power so consumed is substantially reduced using thetwo digital signal processors for performing the respective functionswithin the predetermined period of time in respect of the power thatwould otherwise be required for a single processor to perform the samefunctions during the same time period.

Additionally, and as described above, the supply voltage may also bereduced because the digital signal processors are running at ½ speed anda decrease in clock frequency permits use of lower supply voltages.Power consumption is reduced because power the consumed is directlyproportional to the square of the supply voltage. If the clock frequencyof the digital signal processors is reduced in half, for example,relative to a single processor embodiment using multiplexed inputs, thesupply voltage may also be reduced in half relative in respect of thesupply voltage employed in a single processor embodiment.

Upon detecting an atrial event, DSP system 801 provides an A-eventsignal at output 811. Upon detecting a ventricular event, DSP system 803provides a V-event signal at output 813. The sense amplifier functionsillustrated in FIG. 14 are therefore accomplished using the two DSPsystem embodiment of the present invention shown in FIG. 15, with acorresponding reduction in power consumption in respect of the use of asingle DSP system to accomplish the same functions (such as thoseillustrated in FIG. 12).

Those skilled in the art will recognize that other signals may beprocessed according to the present invention with the same or additionaldigital signal processors and/or systems. For example, such DSP systemsmay be used for T-wave detection, oxygen sensor data analysis, pressuresensor data analysis, cardiac contractility data analysis, EMIdetection, or for processing and analyzing any other signals or datasets may benefit from the use of digital signal processing.

The present invention is compatible with various fabricationtechnologies such as silicon on insulator (SOI), silicon on sapphire(SOS), current mode logic (CML), BICMOS, PMOS and NMOS CMOStechnologies, as well as to conventional silicon CMOS technologies. Thepresent invention as described herein is enabling technology in respectof the employment of multiple DSP systems to perform more functions andcomputations due to the manner in which power consumption may be reducedfor such multiple DSP systems. Moreover, multiple processor baseddesigns may also be implemented in accordance with the present inventiondue to reduced power consumption resulting from supply voltages andclocking frequencies being reduced for various functions andcomputations performed by the processors.

Additionally, as power consumption is reduced, further functionality maybe added to devices in accordance with the present invention to providea device having added functionality yet lower or the same powerconsumption relative to conventional prior art devices. A processor inaccordance with the present invention may perform, for example, variousmorphology detection functions such as differentiation of retrogradeP-waves and antegrade P-waves of EGM waveform; differentiation ofP-waves from far field R-waves; differentiation of AF-A flutter-AT fromsinus tachycardia; differentiation of VT-VF-V flutter from SVT;differentiation of cardiac signals from electromagnetic interference;etc. Also by way of example, various embodiments of the presentinvention may also be employed to detect or filter out electromagneticinterference (EMI) emanating from or generated by theft detectors,conductive signals, RF noise, myopotentials, and the like.

FIG. 16 is a general schematic block diagram of device 600 includinganalog circuitry 602 and digital circuitry 604 (including clock circuit605). The digital circuitry (e.g., CMOS, CML, SOS, SOI, BICMOS, PMOSand/or NMOS technology) has a fixed supply voltage (V_(digital)) appliedthereto from power source 608, which may be any type of electrochemicalcell or battery suitable for use in an implantable medical device andproviding an appropriate supply voltage. Some examples of batteries orcells finding application in respect of the present invention include,but are not limited to, lithium iodine, lithium manganese, nickelcadmium, nickel metal hydride, zinc manganese oxide, zinc silver oxide,zinc mercuric oxide, lithium silver vanadium oxide, lithium ion,divalent silver oxide and silver oxide electrochemical cells andbatteries. At least some of the foregoing chemical systems may requirestepping down of voltage for use in certain embodiments of the presentinvention.

Fixed supply voltage V_(digital) applied for operation of the digitalcircuitry is kept low to reduce power consumption as previouslydescribed herein. Power consumed by the CMOS, CML, SOS, SOI, BICMOS,PMOS and/or NMOS circuitry, for example, is proportional to the squareof the supply voltage. Therefore, a lower supply voltage is necessary toreduce power consumption.

Particularly for implantable devices, however, designing analogcircuitry 602 to function at such low supply voltages is difficult dueto various considerations, such as small circuit headroom, small signalamplitudes (which may effectively reduce amplifier sensitivity), smallsignal-to-noise ratios, reduced common mode rejection ratios (CMRR),reduced transmitted telemetry power, voltage regulation and currentsource problems, and so on.

As such, in accordance with the present invention, device 600 furthermost preferably includes voltage generator circuit 606 to generate atleast one fixed supply voltage (V_(analog)) for application to analogcircuitry 602. Voltage generator circuit 606 is supplied with supplyvoltage V_(digital) to generate supply V_(analog). Voltage generatorcircuit 606 may generate any number of predetermined or fixed voltagesgreater than V_(digital) to supply different analog circuits. Forexample, output circuits may require a larger voltage than otheramplification circuits. Voltage generator circuit 606 will generate both+/− supplies (V_(DD) and V_(SS)) to power only the analog circuitry 602.

Digital circuitry 604 is supplied with the lower voltage V_(digital).For example, as contemplated in the present invention, lower fixed orpredetermined supply voltage V_(digital) is in the range of about 1.1 to1.5 volts at beginning-of-life (BOL) and about 0.8 volts to about 1.0volts at end-of-life (EOL). The generated fixed supply voltageV_(analog) is in the range of about +/−2.0 volts to about +/−3.0 volts.

Level shifter 610 may be used to translate logic and/or control signalsbetween the analog circuitry 602 and the digital circuitry 604. Suchlevel shifting may be required due to the difference in supply voltagebeing applied to the respective digital circuitry 604 and analogcircuitry 602.

As described previously above, with reduction in supply voltage(V_(DD)), threshold voltage (V_(T)) for the circuits is also reduced.With use of lower threshold levels due to lower supply voltages, staticpower consumption losses undesirably increase by several orders ofmagnitude. A back gate bias source 609 may therefore be used to provideback gate bias voltages to digital circuitry 604. In this manner, staticleakage current losses can be minimized because the equivalent higherthreshold voltage has been restored. The back gate bias voltage may beprovided by, for example, a fixed voltage source (e.g., a charge pump)connected to the back gate well via a contact. Alternatively, an activebody bias scheme whereby the voltage source is selectable or adjustableover an appropriate range may be used. Back gate voltages may be appliedin any known manner, such as those previously described herein.

FIG. 17 is a more detailed schematic block diagram of one embodiment ofpacemaker 700 much like that shown in FIG. 9. According to the presentinvention, a lower supply voltage V1 (e.g., 1.1 volt source 710) isapplied to digital circuitry 702 of pacemaker 700 with charge pumpcircuit 706 being used to generate at least one higher supply voltage V2(e.g., 3.0 volts) to be applied to analog circuitry 704 of pacemaker700.

Digital circuitry 702 may, for example, include circuits such as thosedescribed above in reference to pacemaker 300 and FIG. 17. Digitalcircuitry 702 may include, for example, controller/timer and processorcircuit 714 (including a clock circuit 715) or memory circuits such asRAM/ROM circuits 716 for communication with controller/timer andprocessor circuit 714. Such components and functionality are describedherein with reference to FIG. 9.

Analog circuitry 704 may include the analog circuits of pacemaker 300described previously in reference to FIG. 9. Such analog circuits mayinclude, for example, atrial and ventricular sense amplifiers forreceiving A-sense signals from the atrium of heart 764 and for receivingV-sense signals from the ventricle of heart 764. Such sense amplifiercircuits are coupled to leads extending to heart 764 via capacitors C1and C2 to receive the V-Sense (ventricular sense) and A-Sense (atrialsense) signals from heart 764. Sense amplifier circuits then communicatean A-event signal to controller 714 when an atrial event (i.e., anintrinsic atrial event or P-wave) is detected, and communicate a V-eventsignal to controller 714 when a ventricular event (an intrinsic R-wave)is detected. Analog circuitry 704 may also include bandpass filters anddetection circuitry to accomplish such detection. Moreover, analogcircuitry 704 may include circuitry for T-wave detection, such as aT-wave amplifier, bandpass filter, or capture detection circuitry.

Analog circuitry 704 may include various other circuits, such as analogto digital converters (ADCs); voltage reference and current sourcecircuits; telemetry transmission and reception circuitry; sensoramplification circuitry, and bandpass, detection, and drive circuitry tobe used with such sensors (e.g., minute ventilation activity, pressure,temperature, pH, pCO2 or oxygen sensors); ECG amplifiers and bandpassfilters, such as amplifiers for A-sense signals, V-sense signals andT-wave signals to be used for telemetry purposes; output circuits andpump circuits such as those described in U.S. Pat. No. 5,387,228 toShelton; battery monitor circuits; power on reset circuits; and anycircuits generally designed as analog circuits.

FIG. 18 shows an alternative embodiment for at least some of the analogcircuitry 704 described in reference to FIG. 17. The functions of someof the analog circuits, for example sense amplifiers, may be implementedusing circuitry 780 which includes analog circuits 782 (e.g.,preamplifiers, ADC's, etc.) and further includes one or more digitalsignal processors (DSPs) 784 to perform analysis with respect to datacommunicated thereto by way of analog circuits 782. A similarillustrative implementation is described hereinabove in respect of FIG.11. As such, and according to the present invention as described inreference to FIGS. 16 through 18, supply voltage V1 is applied to DSP(s)784 while charge pumped voltage V2 is used as the supply voltage foranalog circuits 782.

Charge pump circuit 706 is used to generate both +/− voltage supplies(V_(DD) and VSS) to power analog circuitry 704. Various configurationsfor charge pump circuit 706 may be used. Charge pump circuit 706 may beimplemented, for example, using the techniques described in U.S. Pat.No. 5,387,228 to Shelton. Charge pump circuit 706 may, for example, beregulated, such as with use of a charge comparator circuit to regulatethe voltage, or charge pump circuit 706 may be unregulated. Theunregulated voltage may vary as the voltage source V1 varies due to lowbattery conditions, for example. Yet further, one or more supplyvoltages may be output from charge pump circuit 706 as voltage V1 ispumped to different amplitudes. More than one supply voltage may beprovided by charge pump circuit 706 or more than one charge pump circuit706 may be employed to provide multiple supply voltages, where eachcharge pumped voltage is greater than supply voltage V1. That is, onecharge pumped voltage may exceed another charged pumped voltage.

Supply voltages V1 and V2 described in reference to FIG. 17 (i.e.,wherein different supply voltages are applied to analog circuitry anddigital circuitry, respectively) are fixed predetermined voltages. Inother words, pumped predetermined fixed voltage V2 is applied to theanalog circuits whenever they are in operation, as opposed to a pumpedvoltage being applied to circuits only when low battery conditions areapparent. Such voltages are determined at the time the circuits aredesigned and do not vary other than possibly when batteries have evenlower states of charge.

Additionally, pacemaker 700 may include a level shifter 708. Levelshifter 708 may be used to translate logic and/or control signalsbetween analog circuitry 704 and controller and processor 714. Suchlevel shifting may be required due to the difference in supply voltagesbeing applied to digital circuitry 702 and analog circuitry 704,respectively. Such a voltage level shifter may be implemented in variousconfigurations. For example, illustrative voltage level shifters aredescribed in U.S. Pat. No. 4,663,701, hereby incorporated by referenceherein in its entirety.

Those skilled in the art will now recognize that the technique ofapplying a lower supply voltage to digital circuitry of a device havinga relatively large charged pumped voltage applied to the analogcircuitry thereof may be applicable to other medical or implantabledevices in a manner similar to that described in reference to apacemaker. Application of different voltages to the analog and digitalcircuitry of the PCD described hereinabove in respect of FIG. 10, forexample, may be employed to reduce power consumption.

Additionally, as power consumption is reduced, further functionality maybe added to devices in accordance with the present invention to providea device having added functionality and yet lower or the same powerconsumption relative to conventional prior art devices. A processor inaccordance with the present invention may perform, for example, variousmorphology detection functions such as differentiation of retrogradeP-waves and antegrade P-waves of EGM waveform; differentiation ofP-waves from far field R-waves; differentiation of AF-A flutter-AT fromsinus tachycardia; differentiation of VT-VF-V flutter from SVT;differentiation of cardiac signals from electromagnetic interference;etc. Also by way of example, various embodiments of the presentinvention may also be employed to detect or filter out electromagneticinterference (EMI) emanating from or generated by theft detectors,conductive signals, RF noise, myopotentials, and the like.

The preceding specific embodiments are illustrative of the practice ofthe invention. It is to be understood, therefore, that other expedientsknown to those skilled in the art or disclosed herein may be employedwithout departing from the invention or the scope of the appendedclaims. For example, the present invention is not limited to the use ofany particular digital or analog circuits. Furthermore, the voltagesapplied need not be at any predefined level, but only need be different.Although a charge pump is preferred for generating the higher supplyvoltage described herein, there may be other voltage generation devicescapable of generating the desired voltage levels for application toanalog circuits. The present invention is also not limited to use inconjunction with pacemakers or PCDs, but may find further application inother relevant areas such as personal computing or telecommunicationswhere low power consumption is desired. The present invention furtherincludes within its scope the use of other techniques described hereinin conjunction with the application of different supply voltages toanalog and digital circuits (such as, for example, just-in-time clockingdevices and methods).

The present invention is also not limited, for example, to the use ofonly two DSP systems, and DSP systems in accordance with the presentinvention may be used with other clock frequency management techniquesdescribed herein (such as multiple clock frequencies for more than onefunction performed by one of the multiple processors). Moreover, thesupply voltage source used for the multiple DSP systems of the presentinvention may include not only discrete supply voltages, but may alsoinclude a source that is varied continuously over a particular range ofvoltages such as by a voltage regulator, with such voltages changed “onthe fly” with corresponding clock frequencies. The present invention isfurther not limited to use in conjunction with pacemakers or PCDs, butmay find further application in other relevant areas where low powerconsumption is desired, such as in the telecommunications and personalcomputing fields, for example. The present invention further includeswithin its scope methods of making and using the features, concepts andcircuitry described hereinabove.

In the claims, means plus function clauses are intended to cover thestructures described herein as performing the recited function and theirequivalents. Means plus function clauses in the claims are not intendedto be limited to structural equivalents only, but are also intended toinclude structures which function equivalently in the environment of theclaimed combination.

I claim:
 1. A method for conserving electrical power consumed by amedical device including one or more analog circuits and one or moredigital circuits, the method comprising the steps of: providing a firstdigital signal processor coupled to at least one of the one or moreanalog circuits of the medical device for receiving analog datarepresentative of at least a first analog input; operating on the analogdata representative of the first analog input using the first digitalsignal processor to perform at least a first function during apredetermined time period, the first digital signal processor operatingat a first clock frequency to perform the first function; providing asecond digital signal processor coupled to at least one of the one ormore analog circuits of the medical device for receiving analog datarepresentative of at least a second analog input; operating of theanalog data representative of the second analog input using the seconddigital signal processor to perform at least a second function duringthe predetermined time period, the second digital signal processoroperating at a second clock frequency to perform the second function;applying a first fixed supply voltage to the one or more digitalcircuits; and generating a second fixed supply voltage for applicationto the one or more analog circuits using the first fixed supply voltage,wherein the second fixed supply voltage is greater than the first fixedsupply voltage, wherein the first and second clock frequencies are suchthat the power consumed by the first and second digital signalprocessors in performance of the first and second functions during thepredetermined time period is less than the power that would be consumedif only one of the first and second digital signal processors were toperform both of the first and second functions within the predeterminedtime period.
 2. The method of claim 1, wherein the first and secondclock frequencies are about equal.
 3. The method of claim 1, wherein thepredetermined time period is a time period based on physiologicalevents.
 4. The method of claim 1, wherein the data representative offirst and second analog inputs are cardiac sense signals.
 5. The methodof claim 1, wherein the method further includes applying a first supplyvoltage to the first digital signal processor based on the first clockfrequency, and further includes applying a second supply voltage to thesecond digital signal processor based on the second clock frequency. 6.The method of claim 5, wherein the first and second clock frequenciesare about equal.
 7. The method of claim 1, wherein the medical devicefurther includes one or more additional digital signal processors, eachfor receiving data representative of at least one analog signal providedby the one or more analog circuits and wherein the method furtherincludes the step of operating on the data representative of the atleast one analog input using the additional digital signal processor atan additional clock frequency to perform at least one additionalfunction during the predetermined time period.
 8. The method of claim 7,wherein at least one of the first and second functions is selected fromthe group consisting of capture detection, R-wave detection, P-wavedetection, T-wave detection, electromagnetic interference detection,oxygen saturation determination, pressure determination, sensor cardiaccontractility determination, cardiac flow determination, telemetryreception and telemetry transmission.
 9. The method of claim 1, whereinthe medical device is a hermetically sealed implantable medical device.10. The method of claim 9, wherein the implantable medical deviceproviding step further comprises the step of providing an implantablemedical device selected from the group consisting of an implantablestimulator, an implantable nerve stimulator, an implantable pacemaker,an IPG, an implantable cardioverter, an implantable PCD, an implantabledefibrillator, an implantable ICD and an implantable drug pump.
 11. Themethod of claim 1, wherein the steps of providing the first and seconddigital processing systems further comprise the steps of providingcircuitry for at least one of the first and second digital processingsystems selected from the group consisting of CMOS circuits, CMLcircuits, SOS circuits, SOI circuits, BICMOS circuits, PMOS circuits andNMOS circuits.
 12. The method of claim 1, wherein the step of generatingthe second fixed supply voltage includes the step of generating thesecond fixed supply voltage using a charge pump circuit.
 13. The methodof claim 1, wherein the first fixed supply voltage ranges between about0.8 volts and about 1.5 volts.
 14. The method of claim 1, wherein thesecond fixed supply voltage ranges between about +/−2.0 volts and about+/−3.0 volts.
 15. The method of claim 1, wherein the method furtherincludes the step of adjusting a back gate bias of at least one of theone or more digital circuits.
 16. The method of claim 1, wherein thestep of providing the one or more digital circuits includes providing atleast one of a processor, a controller and a memory.
 17. The method ofclaim 1, wherein the step of providing the one or more analog circuitsincludes the step of providing at least one of an atrial senseamplifier, a ventricular sense amplifier, a T-wave amplifier, one ormore bandpass filters, one or more detection circuits, one or moresensor amplification circuits, one or more physiological signalamplification circuits, one or more output circuits, a battery monitorcircuit, and a power on reset circuit.
 18. The method of claim 1,wherein the step of providing the one or more digital circuits includesthe step of providing at least one digital signal processor having thefirst supply voltage applied thereto for receiving data representativeof one or more analog signals.
 19. The method of claim 1, wherein thestep of providing the one or more analog circuits includes the step ofproviding at least one amplifier circuit for amplifying the one or moreanalog signals.
 20. The method of claim 1, wherein the method furtherincludes the steps of communicating signals between the one or moreanalog circuit and the one or more digital circuits, and translatingvoltage levels of signals being communicated between the one or moreanalog circuits and the one or more digital circuits.
 21. A method ofconserving electrical power in a medical device, the method comprisingthe steps of: providing a first digital signal processor of the medicaldevice receiving analog data representative of at least a first analoginput; applying a first supply voltage to the first digital signalprocessor for operation on the analog data representative of the atleast first analog input to perform at least a first function during apredetermined time period; providing a second digital signal processorof the medical device receiving analog data representative of at least asecond analog input; applying a second supply voltage to the seconddigital signal processor for operation on the analog data representativeof the at least second analog input to perform at least a secondfunction during the predetermined time period; wherein the first andsecond supply voltages are such that the power consumed by the first andsecond digital signal processors in performance of the first and secondfunctions is less than the power that would be consumed if only one ofthe first and second digital signal processors were to perform both ofthe first and second functions within the predetermined time period. 22.The method of claim 21, wherein the method further includes operatingthe first and second digital signal processors at a first and secondclock frequency, respectively, to control operation of the first andsecond digital signal processors during performance of the respectivefirst and second functions, and further wherein the first and secondclock frequencies are such that the power consumed by the first andsecond digital signal processors during performance of the first andsecond functions is less than the power that would be consumed if onlyone of the first and second digital signal processors were to performboth of the first and second functions within the predetermined timeperiod.
 23. The method of claim 21, wherein the first and second clockfrequencies are about equal.
 24. The method of claim 21, wherein thepredetermined time period is a time period based on physiologicalevents.
 25. The method of claim 21, wherein the data representative offirst and second analog inputs are cardiac sense signals.
 26. The methodof claim 22, wherein the method further includes applying the firstsupply voltage to the first digital signal processor based on the firstclock frequency, and further includes applying the second supply voltageto the second digital signal processor based on the second clockfrequency.
 27. The method of claim 26, wherein the first and secondclock frequencies are about equal.
 28. The method of claim 21, whereinthe medical device further includes one or more additional digitalsignal processors to receive data representative of at least one analoginput, and wherein the method further includes the step of operating onthe data representative of the at least one analog input using theadditional digital signal processor at an additional clock frequency toperform at least one additional function during the predetermined timeperiod.
 29. The method of claim 28, wherein at least one of the firstand second functions is selected from the group consisting of capturedetection, R-wave detection, P-wave detection, T-wave detection,electromagnetic interference detection, oxygen saturation determination,pressure determination, sensor cardiac contractility determination,cardiac flow determination, telemetry reception and telemetrytransmission.
 30. The method of claim 21, wherein the medical device isa hermetically sealed implantable medical device.
 31. The method ofclaim 30, wherein the implantable medical device providing step furthercomprises the step of providing an implantable medical device selectedfrom the group consisting of an implantable stimulator, an implantablenerve stimulator, an implantable pacemaker, an IPG, an implantablecardioverter, an implantable PCD, an implantable defibrillator, animplantable ICD and an implantable drug pump.
 32. The method of claim31, wherein the steps of providing the first and second digitalprocessing systems further comprise the steps of providing circuitry forat least one of the first and second digital processing systems selectedfrom the group consisting of CMOS circuits, CML circuits, SOS circuits,SOI circuits, BICMOS circuits, PMOS circuits and NMOS circuits.
 33. Themethod of claim 31, wherein the medical device includes one or moreanalog circuits to generate the data representative of at least thefirst and second analog inputs, a voltage source coupled to the one ormore analog circuits, and one or more digital circuits coupled to thevoltage source, and further including the methods of: applying a firstfixed supply voltage generated by the voltage source to the one or moredigital circuits; generating a second fixed supply voltage forapplication to the one or more analog circuits using the first fixedsupply voltage.
 34. The method of claim 33, wherein the step ofgenerating the second fixed supply voltage includes the step ofgenerating the second fixed supply voltage using a charge pump circuit.35. The method of claim 33, wherein the first fixed supply voltageranges between about 0.8 volts and about 1.5 volts.
 36. The method ofclaim 33, wherein the second fixed supply voltage ranges between about+/−2.0 volts and about +/−3.0 volts.
 37. The method of claim 33, whereinthe method further includes the step of adjusting a back gate bias of atleast one of the one or more digital circuits.
 38. The method of claim33, wherein the step of providing the one or more digital circuitsincludes providing at least one of a processor, a controller and amemory.
 39. The method of claim 33, wherein the step of providing theone or more analog circuits includes the step of providing at least oneof an atrial sense amplifier, a ventricular sense amplifier, a T-waveamplifier, one or more bandpass filters, one or more detection circuits,one or more sensor amplification circuits, one or more physiologicalsignal amplification circuits, one or more output circuits, a batterymonitor circuit, and a power on reset circuit.
 40. The method of claim33, wherein the step of providing the one or more digital circuitsincludes the step of providing at least one additional digital signalprocessor having the first supply voltage applied thereto for receivingdata representative of one or more analog signals.
 41. The method ofclaim 33, wherein the step of providing the one or more analog circuitsincludes the step of providing at least one amplifier circuit foramplifying the one or more analog signals.
 42. The method of claim 33,wherein the method further includes the steps of communicating one ormore signals between the one or more analog circuits and the one or moredigital circuits, and translating voltage levels of signals beingcommunicated between the one or more analog circuits and the one or moredigital circuits.